Systems and methods for determining biomechanical properties of the eye for applying treatment

ABSTRACT

A system for determining biomechanical properties of corneal tissue includes a light source configured to provide an incident light and a confocal microscopy system configured to scan the incident light across a plurality of cross-sections of corneal tissue. The incident light is reflected by the corneal tissue as scattered light. The system also includes a filter or attenuating device configured to block or attenuate the Rayleigh peak frequency of the scattered light, a spectrometer configured to receive the scattered light and process frequency characteristics of the received scattered light to determine a Brillouin frequency shift in response to the Rayleigh peak frequency being blocked or attenuated by the filter or attenuating device, and a processor configured to generate a three-dimensional profile of the corneal tissue according to the determined Brillouin frequency shift. The three-dimensional profile provides an indicator of one or more biomechanical properties of the corneal tissue.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to: U.S. Provisional Patent Application No. 61/836,211, filed Jun. 18, 2013; U.S. Provisional Patent Application No. 61/836,221, filed Jun. 18, 2013; U.S. Provisional Patent Application No. 61/856,244, filed Jul. 19, 2013; U.S. Provisional Patent Application No. 61/864,087, filed Aug. 9, 2013, the contents of these applications being incorporated entirely herein by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The invention pertains to systems and methods for diagnosing and treating the eye, and more particularly, to systems and methods for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye.

2. Description of Related Art

Cross-linking treatments may be employed to treat eyes suffering from disorders, such as keratoconus. In particular, keratoconus is a degenerative disorder of the eye in which structural changes within the cornea cause it to weaken and change to an abnormal conical shape. Cross-linking treatments can strengthen and stabilize areas of weakness in the structure of the cornea. For example, a photosensitizing agent (e.g., riboflavin) is applied to the cornea as a cross-linking agent. Once the cross-linking agent has been applied to the cornea, the cross-linking agent is activated by a light source (e.g., ultraviolet (UV) light) to cause the cross-linking agent to absorb enough energy to cause the release of free oxygen radicals (e.g., singlet oxygen) and/or other radicals within the cornea. Once released, the radicals form covalent bonds between corneal collagen fibrils and thereby cause the corneal collagen fibrils to cross-link and strengthen and stabilize the structure of the cornea. The success of procedures, such as cross-linking treatment, in addressing eye disorders depends on determining accurately the areas of the eye that require treatment and assessing the results of the treatment.

SUMMARY

According to one aspect of the present invention, a system for measuring biomechanical properties of the eye to at least one of plan, implement, or assess treatments of the eye includes a biomechanical measurement system, a corneal topography system, and an iris imaging system. The eye has an iris and a cornea. The biomechanical measurement system includes a light source configured to provide an incident light and a confocal microscopy system configured to direct the incident light at a plurality of sections of the cornea. The incident light is scattered by the plurality of sections of the corneal tissue. The biomechanical measurement system also includes a spectrometer configured to receive the scattered light and process frequency characteristics of the received scattered light to measure a Brillouin frequency shift in the scattered light. The biomechanical measurement system is configured to generate biomechanical data based on the measured Brillouin frequency shift. The corneal topography measurement system is configured to measure a corneal topography of the eye and generate corneal topography data indicative of the measured corneal topography. The iris imaging system is configured to image the iris and generate iris image data indicative of the imaged iris. The system also includes one or more processors communicatively coupled to the biomechanical system, the corneal topography system, and the iris imaging system. The one or more processors includes a processor clock. The system further includes one or more memory devices storing instructions that, when executed by the one or more processors, cause the one or more processors to generate time stamp data, based on the processor clock, for each of the biomechanical data, the corneal topography data, and the iris image data, store the biomechanical data with the associated time stamp data in the one or more memory devices, store the corneal topography data with the associated time stamp data in the one or more memory devices, and store the iris image data with the associated time stamp data in the one or more memory devices. The instructions further cause the one or more processors to, for each of the biomechanical data, determine which of the iris image data has the same associated time stamp data and, for each of the corneal topography data, determine which of the iris image data has the same associated time stamp data. The instructions still further cause the one or more processors to generate three-dimensional voxel data by correlating each of the biomechanical data with each of the corneal topography data determined to have the same associated iris image data. Each of the three-dimensional voxel data includes an indication of at least one of the biomechanical data, at least one of the corneal topography data, and at least one of the iris image data.

According to another aspect of the present invention, a system for determining biomechanical properties of corneal tissue includes a light source configured to provide an incident light and a confocal microscopy system configured to scan the incident light across a plurality of cross-sections of the corneal tissue. The incident light is reflected by the plurality of cross-sections of corneal tissue as scattered light. The system also includes a filter or attenuating device configured to block or attenuate the Rayleigh peak frequency of the scattered light, a spectrometer configured to receive the scattered light and process frequency characteristics of the received scattered light to determine a Brillouin frequency shift in response to the Rayleigh peak frequency being blocked or attenuated by the filter or attenuating device, and a processor configured to generate a three-dimensional profile of the corneal tissue according to the determined Brillouin frequency shift. The three-dimensional profile provides an indicator of one or more biomechanical properties of the corneal tissue.

According to still another aspect of the present invention, a method for measuring biomechanical properties of the eye to at least one of plan, implement, or assess treatments of the eye includes directing, via a confocal microscopy system, an incident light from a light source at plurality of sections of the cornea. The incident light is scattered by the plurality of sections of the corneal tissue. The eye has an iris and a cornea. The method also includes receiving the scattered light in a spectrometer, processing frequency characteristics of the received scattered light to measure a Brillouin frequency shift in the scattered light, determining biomechanical data based on the measured Brillouin frequency shift, measuring a corneal topography of the eye, determining corneal topography data indicative of the measured corneal topography, imaging, via an image capture device, the iris, determining iris image data indicative of the imaged iris, determining, based on a processor clock provided by one or more processors, time stamp data for each of the biomechanical data, the corneal topography data, and the iris image data, storing the biomechanical data with the associated time stamp data in one or more memory devices, storing the corneal topography data with the associated time stamp data in the one or more memory devices, and storing the iris image data with the associated time stamp data in the one or more memory devices. The method further includes, for each of the biomechanical data, determining which of the iris image data has the same associated time stamp data. The method also includes, for each of the corneal topography data, determining which of the iris image data has the same associated time stamp data. The method still further includes determining three-dimensional voxel data by correlating each of the biomechanical data with each of the corneal topography data determined to have the same associated iris image data. Each of the three-dimensional voxel data includes an indication of at least one of the biomechanical data, at least one of the corneal topography data, and at least one of the iris image data.

Additional aspects of the invention will be apparent to those of ordinary skill in the art in view of the detailed description of various embodiments, which is made with reference to the drawings, a brief description of which is provided below.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram of an example system for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye according to some aspects of the present invention.

FIG. 2 is a schematic diagram of an example system for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye according to additional aspects of the present invention.

FIG. 3 is a schematic diagram of an example confocal scanning microscopy head for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye according to some aspects of the present invention.

FIGS. 4A-4C illustrate stereoscopic cameras and an optical component for the confocal scanning microscopy head illustrated in FIG. 3

FIG. 5 is a flow chart of an example method for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye according to some aspects of the present invention.

FIG. 6 is a schematic diagram of an example spectrometer according to some aspects of the present invention.

FIG. 7 is a schematic diagram of example approaches for blocking or attenuating the Rayleigh peak in scattered light according to some aspects of the present invention.

While the invention is susceptible to various modifications and alternative forms, a specific embodiment thereof has been shown by way of example in the drawings and will herein be described in detail. It should be understood, however, that it is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit of the invention.

DETAILED DESCRIPTION

Aspects of the present invention relate to systems and methods for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye. According to some aspects, the systems and methods provide an approach to developing and implementing a plan for treating an eye disorder. For example, the systems and methods can be employed to accurately determine areas of corneal weakness so that cross-linking treatment can be applied to the most appropriate areas.

According to aspects of the present invention, systems and methods employ the principle of Brillouin scattering to determine biomechanical properties of the eye. Brillouin scattering involves the inelastic scattering of incident light (photons) by thermally generated acoustic vibrations (phonons). Thermal motions of atoms in a material (e.g., solid, liquid) create acoustic vibrations, which lead to density variations and scattering of the incident light. The scattering is inelastic, which means that the kinetic energy of the incident light is not conserved. The photon either loses energy to create a phonon (Stokes) or gains energy by absorbing a phonon (Anti-Stokes). The frequency and path of the scattered light differ from those of the incident light. The frequency shift, known as the Brillouin shift, is equal to the frequency of the scattering acoustic vibration and provides information regarding the properties of the material. In particular, the systems and methods described herein evaluate the Brillouin shift to measure the biomechanical, e.g., viscoelastic, properties of corneal tissue.

Accordingly, FIG. 1 illustrates an example Brillouin spectroscopy system 10 for determining biomechanical properties of an eye via Brillouin scattering. As shown in FIG. 1, the system employs confocal scanning microscopy (CSM). A light source 100 provides incident light for generating Brillouin scattering in an eye 1. The light source 100 may provide a laser with an ultraviolet (UV), visible, or near infrared (NIR) wavelength, depending on the resolution required. In an example embodiment, the light source 100 includes a narrowband linewidth diode laser source (approximately 100 kHz-4 MHz) that generates a laser with a NIR wavelength of approximately 780 nm. This wavelength provides an advantageous compromise of spatial and depth resolution while not being too bright for the patient. The light source 100 is coupled to a single mode beam splitting fiber coupler 115 with a specific input/output power ratio (e.g., approximately 5-20%) and a narrowband frequency (e.g., approximately 100 kHz to approximately 4 MHz). With this beam spitting fiber coupler 115, a percentage of the light from the light source 100 based on the input/output power ratio (e.g., approximately 5-20%) passes to a CSM fiber 120 that is coupled to a CSM head 200, while the rest of the light (e.g., approximately 80-95%) passes to a beam dump fiber 125 which is measured with a photodiode 130. It is understood that different input/power ratios may be employed. In addition, although the example of FIG. 1 employs the beam spitting fiber coupler 115, other embodiments can split the light from the light source 100 using any combination of optical devices, such as a beam splitter, a half wave plate/polarizing beam splitter/quarter wave plate combination, etc.

The CSM head 200 includes a set of scanning galvo minors 205 and a confocal imaging lens 210. In some embodiments, to achieve a consistent flat field, the confocal imaging lens 1210 may be an F-theta lens which may have a focal length on the order of approximately 1 cm to approximately 20 cm. In general, however, the system 10 employs a confocal imaging lens 210 with an appropriate focal length to provide a suitable working distance to the eye 1. The light passing through the fiber 120 is collimated and directed through the set of scanning galvo mirrors 205 where it is then collimated to a spot on the eye 1 via the confocal imaging lens 210. The set of scanning galvo minors 205 is used in combination with the confocal imaging lens 210 to scan multiple points of the cornea in enface X-Y slices. For example, a first enface X-Y scan of a specified number of points in a specified pattern is made in a plane starting at the apex of the cornea. The CSM head 200 is then stepped a known distance in the Z-direction (toward the eye 1) to create a second additional enface X-Y scan of the cornea. Subsequently, the CSM head 200 is iteratively stepped in the Z-direction to create additional (e.g., third, fourth, etc.) enface X-Y scans of the cornea for the full thickness of the cornea out to a user specified diameter. Specific regions of interest may be specified for the scanning based on corneal topography images or other corneal analysis.

It should be understood that the scanning pattern is not restricted to strictly enface imaging. For example, the system can first scan in the z dimension and then step in X-Y dimensions or some other raster scan pattern. Additionally, for example, the first enface X-Y scan can be made in a plane starting at a user defined diameter and then stepped toward the apex of the cornea.

The incident light from the light source 100 experiences scattering when it interacts with the eye 1, i.e., corneal tissue. The light scattered back from the spot of incident light on the eye 1 is directed back through the confocal imaging lens 210 and the set of galvo mirrors 205 and into the beam spitting fiber coupler 115 where the fiber core acts like a pinhole in a confocal scanning microscope. The scattered light is then transmitted back through the beam splitting fiber coupler 215 where approximately 80-95% of the scattered light is directed in a spectrometer single mode fiber 135, while the rest of the scattered light (approximately 5-20%) heads to the laser. The laser is equipped with an optical isolator 140 so that the scattered light from the eye 1 does not create feedback within the laser resonator causing potential laser instability.

The spectrometer input fiber 135 extends to a spectrometer system 300 and may have any length to separate spectrometer system 300 practically from other aspects of the system 10, e.g., the light source 100, the CSM head 200, etc. The spectrometer system 300 includes a tilted virtual imaged phased array (VIPA) 305 of a known thickness and free spectral range. The VIPA 305 receives the scattered light from spectrometer input fiber 135 via a lens or lens system.

As described above, the incident light from the light source 100 experiences scattering when it interacts with the corneal tissue. This scattering includes Brillouin scattering and the resulting Brillouin shift can be analyzed to determine biomechanical, e.g., viscoelastic, properties of the corneal tissue. The scattering, however, also includes the additional phenomenon of Rayleigh scattering, which involves elastic scattering of the incident light. This elastically scattered light has the same frequency as the incident light. In addition, the elastically scattered light is orders of magnitude more intense than the Brillouin-scattered light, and the frequency shift between the scatter fractions is very low, e.g., only a few GHz. As such, Brillouin spectroscopy requires separating the Brillouin-scattered light frequencies from the Rayleigh-scattered light frequency.

The system 10 employs the VIPA 305 to separate the Brillouin-scattered light frequencies (Stokes and Anti-Stokes) from the Rayleigh-scattered light frequency. After separation, the light exits the VIPA 305 where it is collected and collimated with a lens or lens system and imaged onto a line scan camera 315 (properly filling the pixels of the line scan camera 315). The pixels of the line scan 315 are calibrated for a specific frequency shift per pixel (e.g., 0.15 GHz/px). In this way, the line scan camera 315 acts like a ruler that measures the changing shifts of the Brillouin frequencies with respect to the Rayleigh frequency of the cornea. The line scan camera 315 can be calibrated by measuring standards with known Brillouin frequency shifts. The line scan camera 315 has a given pixel array dimension typically with 512, 1024, or 2048 pixels that is very sensitive to the wavelength of the illumination to allow for short integration times. Therefore, the line scan camera 315 may provide specific methods for increasing sensitivity such as cooling, increased pixel size, etc.

The shift in frequency measured by the line scan camera 315 between the Brillouin frequencies (Stokes and Anti-Stokes) and the Rayleigh frequency is a measure of the bulk modulus or stiffness properties of the cornea. Thus, with the Brillouin spectroscopy system 10, a mapping of the biomechanical properties of the cornea can be made. Mappings can be conducted and compared for normal, diseased, and treated (e.g., cross-linking treated) corneas as well as a quantitative measure of anterior segment anatomy.

A specific approach for increasing sensitivity and shortening exposure times to allow for increased data acquisition rates involves either blocking or attenuating the Rayleigh peak. This allows the highest gain on the line scan camera 315 to be utilized without saturation. Example approaches for blocking or attenuating the Rayleigh peak are summarized in FIG. 7. In step 505, scattered light is received from a confocal imaging system directed at an eye, and after the Raleigh peak is blocked or attenuated (steps 510A, 510B, or 510C), the scattered light is eventually imaged onto line scan camera 315 in step 515.

One example approach 505A shown in FIG. 7 for blocking the Rayleigh peak involves employing a Rubidium vapor cell in-line with the optical system. As shown in FIG. 1, for example, the scattered light from the spectrometer input fiber 135 passes through a Rubidium vapor cell 310, which is tuned to block the Rayleigh frequency. In particular, the Rubidium vapor cell 310 is tuned to the Rayleigh frequency with a known amount of absorption to match the amplitude of the Brillouin frequencies. As such, the Rubidium vapor cell tuned to the Rayleigh frequency acts as a narrowband notch filter, eliminating this peak from the spectrum hitting the line scan camera 315. Advantageously, the Rubidium vapor cell removes noise and improves signal-to-noise ratio. The Brillouin frequency shift is then measured by taking the frequency difference between the Stokes and Anti-stokes Brillouin peaks and dividing by two.

Another example approach 505B shown in FIG. 7 for blocking the Rayleigh peak puts a narrow physical obscuration over the line scan camera pixels associated with the Rayleigh peak. Again, the Brillouin frequency shift described above is measured by taking the frequency difference between the Stokes and Anti-stokes Brillouin peaks and dividing by two.

A similar approach 505C shown in FIG. 7 for attenuating the Rayleigh peak involves putting a narrow physical neutral density filter or attenuator over the line scan camera pixels associated with only the Rayleigh peak. In this way, the Rayleigh peak is attenuated to the same order of magnitude as the Brillouin peaks. As such, the frequency shift between the Stokes, Anti-Stokes, and Rayleigh peaks can be better determined through redundant measure allowing for higher noise floor signal and higher sensitivity. In addition, the relative amplitude of the peaks between the Stokes, Anti-Stokes, and Rayleigh peaks may be used to help increase and normalize the contrast associated with morphological imaging of the corneal structures.

The ratio of the Rayleigh peak to the Brillouin peak is called the Landau-Placzek Ratio and is a measure of the turbidity of the tissue. Therefore, by tuning the Rubidium absorption filter to absorb a predicted amount of the Rayleigh frequency or using a partially reflective/transmitting obscuration, a quantitative measure of the turbidity of the cornea can be made. This is essentially a densitometry measure of the cornea. The densitometry of the cornea in conjunction with the biomechanical properties of the cornea gleaned from the Brillouin frequency shift may give an enhanced measure of corneal disease states as well as a better measure of the amount of corneal cross-linking imparted to the cornea.

Accordingly, aspects of the present invention employ a confocal scanning microscopy system and a spectrometer system to measure the frequency differences between Brillouin-scattered light and the Rayleigh-scattered light. In the case of the cornea, the Brillouin shift is on the order of approximately 2 GHz to approximately 10 GHz. As described above, Brillouin spectroscopy systems and methods can be employed to determine accurately areas of corneal weakness so that cross-linking treatment can be applied to the most appropriate areas. Such systems and methods may also be used during and/or after the cross-linking treatment for real-time monitoring of the cross-linking activity as well as healing processes over time. Through the scanning process, a real-time image of the cornea can be constructed allowing for anatomical measurements of various tissues such as tear film, epithelium, stroma, etc.

During the scanning process, the patient's head may be stabilized through the use of a head and chin rest system (not shown) typically used for many ophthalmic diagnostic and therapeutic devices. The head and chin rest system holds the patient's head and eye socket relatively still. The patient's eye, however, can still move within the eye socket. To address such movement of the eye 1, the system 10 may employ a stereo range finding (SRF) module 250 that includes a pair (or pairs) of cameras 255 separated by a known distance viewing the same field of view. As the spot of incident light moves across the cornea, the scanning pattern is seen by the cameras. The disparity between the images from the cameras 255 and the expected position based on scanning parameters is a measure of the X-Y-Z position of the particular X-Y scan (defined as the X-Y-Z composite scan). The X-Y-Z composite scan can then be placed in a series of predetermined three dimensional bins (or voxels) for the cornea. The system captures data until enough X-Y-Z composite scans have filled all the bins. These bins are then averaged and the composite corneal mapping of the Brillouin frequency shifts is used to calculate the viscoelastic mapping and other quantitative measures of the cornea. As such, the system 10 continues to scan until all the data is collected, automatically stopping only when all the bins have been filled. In general, the bins represent different three-dimensional sections of the cornea and measurements for each section are associated with the respective bin. Any number of measurements (0, 1, 2, 3, etc.) can be recorded for each bin as desired and the bins can have the same or different numbers of measurements. In addition, the sizes of the bins can vary from very course (e.g., 1 mm×1 mm×100 μm) to very fine (e.g., 25 μm×25 μm×25 μm) depending on requirements for analysis. For example, routine examination of a healthy eye may permit the use of more coarsely sized bins, which typically means that there are fewer bins and less time is required to obtain measurements. The bins can be defined across any area of the cornea, e.g., approximately 9.5 mm to 14 mm across the coma extending to the sclera.

Accounting for the various amounts of motion of the eye 1 allows the patient to be positioned and the eye 1 to be scanned in a single measurement period. This approach reduces, if not eliminates, the number of repeat measurements requiring repositioning of the patient, in contrast to other diagnostic systems such as corneal topography systems which often require the patient to be repositioned several times to obtain a quality image.

It should be understood that, according to additional and/or alternative aspects of the present invention, the corneal topography can be measured by other systems. For example, an alternative to utilizing the scanned beam is to project a static grid at a different wavelength to determine the three dimensional volume of the cornea using the same stereo pair cameras.

Mapping of the Brillouin shifts gives a biomechanical mapping of the viscoelastic properties of the tissue. The mapping of the Brillouin shifts may be registered using the pair of cameras 255 which allows for three dimensional registration of the points as they are taken, especially in the case where the data acquisition is slow. In this manner, eye movement taken into account.

Referring to FIG. 2, an alternative embodiment for a Brillouin spectroscopy system 1010 is illustrated. In contrast to the system 10 shown in FIG. 1, the system 1010 employs a technique similar to an optical coherence tomography (OCT) system 1305. OCT is an optical signal acquisition and processing method. It captures micrometer-resolution, three-dimensional images from within optical scattering media (e.g., biological tissue). Optical coherence tomography is an interferometric technique, typically employing near-infrared light. The use of relatively long wavelength light allows it to penetrate into the scattering medium. Depending on the properties of the light source, optical coherence tomography can achieve sub-micrometer resolution.

As shown in FIG. 2, the system 1010 includes a swept source laser system 1100, which, for example, may provide a bandwidth of approximately 80 nm to approximately 150 nm or more. The wavelength of the laser from the laser system 1100 may be ultraviolet (UV), visible, or near-infrared (NIR) depending on the resolution required. The laser system 1100 is coupled to a single mode optical fiber 1105 with narrowband frequencies for the individual lines of the swept source. In one embodiment, a laser provides a NIR bandwidth, which advantageously offers sufficient spatial and depth resolution while not being too bright for the patient.

In an OCT system, the laser from the optical fiber 1105 would be split by a beamsplitter into two arms, a sample arm (directed to the sample of interest) and a reference arm (usually a minor), where the light reflected back from the sample through the sample arm and reference light in the reference are produce an interference pattern. In the embodiment of FIG. 2, the laser from the optical fiber 1105 may be split by a beamsplitter 1115 into a sample arm 1120 and a reference arm 1130. The sample arm 1120 is employed for Brillouin spectroscopy. In particular, the sample arm 1120 includes a CSM head 1200. The CSM head 1200 includes a set of scanning galvo mirrors 1205 and a confocal imaging lens 1210. In some embodiments, to achieve a consistent flat field, the confocal imaging lens 1210 may be an F-theta lens which may have a focal length on the order of approximately 1 cm to approximately 20 cm. In general, however, the system 1010 employs a confocal imaging lens 1210 with an appropriate focal length to provide a suitable working distance to the eye 1. The F-theta lens may also have a large chromatic aberration. The light in the sample arm 1120 is directed through the set of scanning galvo mirrors 1205 where it is then collimated to a spot on the eye 1 via the confocal imaging lens 1210. The set of galvo mirrors 1205 is used in combination with the confocal imaging lens 210 to scan multiple points of the cornea in enface X-Y slices. Enface X-Y scans of a specified number of points in a specified pattern are made in planes starting at the apex of the cornea. As the swept source laser is then scanned, this naturally generates scans along the Z-direction through the tissue. The length of the Z scan is determined by the design parameters of the individual components and is optimized to meet the design criteria of the tissue being measured.

The incident light from the light source 1100 experiences scattering when it interacts with the eye 1, i.e., corneal tissue. The light scattered back from the spot of incident light on the eye 1 is directed back through the confocal imaging lens 1210 and the set of galvo minors 1205.

The system 1010 includes a spectrometer system 1300. Rather than employing a VIPA to identify and separate frequencies in the scattered light, however, the spectrometer system 1300 employs a modulated fiber Bragg grating (FBG) 1125 in the sample arm 1120, which may have any number of grating structures to match the conditions of the desired imaging of the tissue. A radio frequency source 1127 is employed to modulate the FBG through stress induction where the grating period is modulated at very high frequencies. High speed electronics are utilized to analyze the output signals.

Raman scattering is another phenomenon involving inelastic scattering processes of light with vibrational properties of matter. The detected frequency shift range and type of information extracted from the sample, however, are different. Brillouin scattering denominates the scattering of photons from low-frequency phonons, while for Raman scattering, photons are scattered by interaction with vibrational and rotational transitions in single molecules. Therefore, Brillouin scattering and Raman scattering provide different information about the sample. Raman spectroscopy is used to determine the chemical composition and molecular structure, while Brillouin scattering measures properties on a larger scale, such as the elastic behavior. The fiber structure and modulation of the FBG 1125 is matched and made in such a way as to create a super heterodyned beat frequency between the Stokes and Anti-Stokes peaks in the Brillouin scattering. In particular, the radio frequency source 1127 can be modulated to sweep through a range of frequencies to identify a beat frequency associated with the Stokes and Anti-Stokes peaks. In particular, the radio frequency source 1127 can be similarly modulated to sweep through a range of frequencies to identify a beat frequency associated with the Raman peaks. This beat frequencies associated with the Stokes and Anti-Stokes peaks and the Raman peaks can then be used to determine the Brillouin and Raman shifts. Mapping of the Brillouin and Raman shifts give a morphological and biomechanical mapping of the properties of the tissue.

Referring now to FIG. 3, a schematic diagram of an alternative example CSM head 200′ is illustrated according to some aspects of the present invention. The CSM head 200′ advantageously integrates aspects of the Brillouin measurement components described above as well as corneal topography measurement components and iris imaging components for the system 10, 1010. With respect to Brillouin aspects of the system 10, 1010, the CSM head 200′ can include a set of scanning galvo mirrors 205′, a beam expander 260′, and a confocal imaging lens 210′ (e.g., a F-theta lens). The light from the light source 100, 1100 is received in the CSM head 200′ and directed to the set of scanning galvo minors 205′. The light can be collimated prior to being received in the CSM head 200′ or, alternatively, the CSM head 200′ can include optical components for collimating the light that is directed to the set of scanning galvo mirrors 205′. The set of scanning galvo mirrors 205′ are communicatively coupled to a processor(s) 5 that is configured to control the X-Y positioning of the light relative to the target corneal tissue. The collimated light from the set of scanning galvo minors 205′ is then directed to the beam expander 260′, which enlarges the collimated light. The enlarged collimated light is directed from the beam expander 260′ to the confocal imaging lens 210′, which focuses the light to a focal plane within the corneal tissue (i.e., a Z-dimension distance). As further illustrated in FIG. 3, the light scattered by the corneal tissue is collected by the confocal imaging lens 210′, passed back through the optical components of the CSM head 200′, and directed to the spectrometer system 300, 1300 for analysis. The measured biomechanical property information can be determined by the processor(s) 5 and stored in a memory as biomechanical data (e.g., viscoelastic data).

With respect to corneal topographic aspects of the system, the CSM head 200′ includes the plurality of stereoscopic cameras 255A′-255D′ configured to capture images of the corneal tissue. As shown in FIGS. 4A-4C, four stereoscopic cameras 255A′-255D′ are located around the confocal imaging lens 210′ at 90 degree angles relative to each other. It should be understood that more or fewer stereoscopic cameras 255A′-255D′ can be utilized according to some alternative aspects of the present invention. The stereoscopic cameras 255A′-255D′ capture respective images of the corneal tissue and the iris of the eye 1, which can be processed (e.g., by analyzing disparities between two or more images via the processor(s) 5) to determine information (e.g., an elevation map) for the anterior surface of the cornea and the posterior surface of the cornea. This corneal surface information can be further processed to determine the corneal pachymetry and, thus, the corneal topography of the eye 1. The measured corneal topography can be determined by the processor(s) 5 and stored in the memory as corneal topography data.

It should be understood that, according to additional and/or alternative aspects of the present invention, the corneal topography can be measured differently. For example, an alternative to utilizing the scanned beam is to project a static grid at a different wavelength to determine the three dimensional volume of the cornea using the same stereo pair cameras.

With respect to the iris imaging aspects of the system, the CSM head 200′ includes an image capture device 265′ (e.g., a charge-coupled device (CCD)) and imaging optics 270′ for capturing an image of the iris. The processor(s) 5 can determine and store the iris image information as iris image data in the memory. The iris image data provides an indication of the orientation of the eye 1 (i.e., the cornea and the iris) as will be described in greater detail below. Additionally, for example, the iris image data can be utilized for additional X-Y dimension and rotational tracking of the eye 1.

The CSM head 200′ can further include a light fixation system 275′ that is configured to assist in aligning the target eye with respect to the optical components of the CSM head 200′ (e.g., the image capture device 265′, the stereoscopic cameras 255A′-255D′, and the confocal imaging lens 210′). The light fixation system 275′ is configured to project a target light onto an optical component (e.g., a beamsplitter) within the field of view of the target eye. Focusing on the visual target provided by the target light aligns the patient's eye with the optical components of the CSM head 200′. The first, second, third and fourth order Purkinje images of the fixation may be utilized for additional X-Y dimension and rotational tracking of the eye.

The CSM head 200′ in concert with the other optical components (e.g., the spectrometer 300, 1300) of the system 10, 1010 provides an integrated system configured to determine both biomechanical data and corneal topography data for an eye. While these distinct types of data can be analyzed independently of each other to inform the conditions of a patient's eye, the systems and methods of the present invention can advantageously correlate the distinct data sets to develop a significantly improved treatment plan or assessment of eye conditions. For example, the systems and methods of the present invention can correlate the biomechanical data to the corneal topography data to indicate the viscoelastic properties (e.g., corneal strength) associated with particular anatomical features indicated by the topography data.

A problem is presented, however, in that the biomechanical data and the corneal topography data may not be directly correlated. For example, the biomechanical data derived from the measured Brillouin scattering frequencies and the corneal topography data derived from the captured stereographic images may be captured at different points in time or over different durations. Because the patient's eye may move during the measurement procedures, the position and/or orientation of a map of the biomechanical data may differ from that of the corneal topography data. Additionally, for example, while the biomechanical data is derived from a confocal system that scans point by point over successive X-Y planes stepped in a Z direction, the corneal topography data can be derived from one or more stereographic images captured over one or more areas of the cornea.

In the systems and methods described herein, a clock is maintained (e.g., via the processor(s) 5) so that all measurements for the biomechanical data and the corneal topography data are made at known times. Additionally, the iris image capture system 265′, 270′ obtains the iris image data at all known times for which the biomechanical data and the corneal topography data is measured. Because the iris has distinct anatomical features, the iris image data provides an indication of the orientation of the eye 1 (and, thus, the corneal tissue) at each point in time. Accordingly, the iris image data at each known point in time is utilized to provide a common frame of reference against which the biomechanical data and corneal topography data can be translated. In other words, the biomechanical data and the corneal topography data can be aligned against the iris image data to generate a set of 3D voxel data representing at least the biomechanical data, corneal topography data, and iris image data for the eye 1. The 3D voxel data thus correlates the measured biomechanical data, corneal topography data, and iris image data.

The 3D voxel data can be processed (e.g., via the processor(s) 5) to generate a treatment plan for correcting a condition of the eye 1. As one non-limiting example, a finite element analysis can be employed to create the treatment plan. Such a treatment plan can provide a new detailed analysis of how the viscoelastic properties (or other biomechanical properties) of the eye 1 may correspond to the anatomical features indicated by the corneal topography. As such, a more informed and effective treatment plan or eye condition assessment can be developed by the systems and methods of the present invention.

According to further aspects of the present invention, the treatment plan can be programmed into an eye treatment system to correct a condition of the eye 1. For example, the eye treatment system can include a cross-linking system, a LASIK system, a thermokeratoplasty system, combinations thereof, and/or the like. One non-limiting example of a suitable cross-linking system is the PIXL system manufactured by AVEDRO, Inc. (Waltham, Mass.). The eye treatment system includes an eye tracking system that is configured to monitor the patient's iris.

Advantageously, because the treatment plan data is based on the 3D voxel data and thus the iris data, the eye treatment system is automatically aligned to the treatment plan data based on the real-time monitoring of the patient's iris by the eye treatment system. That is, the real-time imagery obtained by the eye treatment system can be aligned with the iris image data of the treatment plan to automatically match patterned eye treatment therapies applied by the eye treatment system to the patient's cornea. For example, the patterns of photoactivating light applied by the PIXL system to the cornea to initiate cross-linking of the corneal fibers can be automatically determined, oriented, and aligned with the patient's cornea based on the real-time monitoring of the patient's eye and the treatment plan data. As shown in FIG. 3, the processor(s) 5 may provide 3D voxel data to a treatment system 7, for example, a cross-linking treatment system that determines a desired pattern of cross-linking activity for the cornea and applies photo-activating light accurately according to the pattern. Approaches for patterned application of photo-activating light can be found, for example, in U.S. patent application Ser. No. 13/438,705, filed Apr. 3, 2012, the contents of which are incorporated entirely herein by reference.

Notably, this automatic alignment of the eye treatment system to the eye treatment plan can mitigate problems associated with cyclotorsion. For example, if a patient is sitting upright during an initial measurement by the system 10 but laying down during the eye treatment, cyclotorsion can cause the cornea to be in different rotational orientations with respect the system 10 as compared to the eye treatment system. This variance in rotational orientation must be accounted for to accurately apply the eye treatment based on the eye treatment plan. As described above, the systems and methods of the present invention can automatically account for such rotational misalignment.

Referring now to FIG. 5, a flow chart for an example method 400 for measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye 1 is illustrated according to some aspects of the present disclosure. At step 412, the biomechanical data is measured for a cornea. As described above, the biomechanical data can be measured by a CSM head (e.g., the CSM head 200 or the CSM head 200′) and a spectrometer (e.g., the spectrometer 300 or the spectrometer 1300). The clock provided by the processor(s) 5 generates time data such that each biomechanical data point measured is associated with a known measurement time. The biomechanical data and the associated time data can be stored in a memory.

At step 414, the corneal topography data is measured for the cornea. As described above, the corneal topography data is measured by the plurality of stereoscopic cameras 255′ at known measurement time(s). The corneal topography data and the associated time data can be stored in the memory.

At step 416, the iris image data is obtained for all known times at which the biomechanical data is measured and all known times at which the corneal topography data is measured. As described above, the iris image data can be obtained by the image capture device 265′ having a field of view configured to be aligned with the eye 1. The iris image data and the associated time data can be stored in the memory.

At step 418, each point of biomechanical data is correlated with the iris image data that was captured at the same time that the biomechanical data was measured. Thus, each point of biomechanical data can be correlated with the respective iris image data that was obtained at the measurement time associated with that point of biomechanical data.

At step 420, the corneal topography data is correlated with the iris image data that was captured at the same time that the corneal topography data was measured. This can be achieved by correlating the topography data to the iris image data based on the time data associated with each data set.

Accordingly, after step 418 and step 420, the biomechanical data and the corneal topography data can be cross-referenced against a common frame of reference provided by the iris image data associated with both the biomechanical data and the corneal topography data. At step 422, the 3D voxel data is generated by correlating the biomechanical data with the corneal topography data based on the respectively associated iris image data. The 3D voxel data thus provides a three dimensional mapping of the biomechanical data, the corneal topography data, and the iris image data.

At step 424, the 3D voxel data can be utilized to develop a treatment plan. The treatment plan is thus, in part, based on the iris image data, which can be subsequently utilized during an eye therapy procedure to ensure that the treatment plan is precisely applied to the eye 1 despite movement of the eye 1.

At step 426, the treatment plan is programmed into an eye treatment system. At step 428, the eye treatment system applies an eye therapy according to the treatment plan. For example, the eye treatment system can include a cross-linking system, a LASIK system, a thermokeratoplasty system, combinations thereof, and/or the like. One non-limiting example of a suitable cross-linking system is the PIXL system manufactured by AVEDRO, Inc. (Waltham, Mass.). The eye treatment system includes an eye tracking system that is configured to monitor the patient's iris. As described above, the application of the eye therapy can include tracking the iris to automatically apply the eye therapy in proper orientation and alignment with the treatment plan (based on the iris image data aspects of the 3D voxel data underlying the treatment plan).

FIG. 5, described by way of example above, represents one algorithm that corresponds to at least some instructions executed by the processor(s) 5 to perform the above described functions associated with the described concepts. It is also within the scope and spirit of the present concepts to omit steps, include additional steps, and/or modify the order of steps presented above. Additionally, it is contemplated that one or more of the steps presented above can be performed simultaneously.

According to some aspects of the present invention, the 3D voxel data can be determined prior to any eye treatment therapy being applied to the eye 1. In such instances, the 3D voxel data can be utilized to diagnose particular eye conditions of the eye 1. Additionally, in such instances, the 3D voxel data can be utilized to determine the treatment plan as described above.

According to additional and/or alternative aspects, the 3D voxel data can be determined during an eye therapy procedure. For example, the 3D voxel data can be utilized to monitor iterative changes to the biomechanical and/or topographic properties of the eye 1 as the eye therapy is being applied. In some instances, the 3D voxel data can be used as feedback to iteratively determine and/or adjust a treatment plan based on an analysis of the 3D voxel data. In other words, the systems 10, 1010 described and illustrated herein can be employed as a feedback system to iteratively and/or continuously control aspects of the eye therapy being applied to the eye 1.

It is contemplated that the feedback provided by the systems and methods of the present invention can be utilized to determine when milestones are achieved during an eye therapy procedure. For example, during a cross-linking procedure, a first pattern of photoactivating light can be applied until the processor(s) 5 determines that the 3D voxel data is indicative of a first shape change (i.e., a first milestone), then a second pattern can be applied until the processor(s) 5 determines that the 3D voxel data is indicative of a second shape change, and so on. It should be understand that other eye therapy procedure parameters can be similarly controlled based on the 3D voxel data determined and processed as feedback by the systems and methods of the present invention.

According to other additional and/or alternative aspects, the 3D voxel data can be determined after an eye therapy procedure. For example, the 3D voxel data can be utilized to verify whether the eye therapy achieved the intended result. As another example, the 3D voxel data can be utilized to comparatively analyze the post-operative conditions of the eye 1 relative to the pre-operative conditions. Additionally, for example, the 3D voxel data can be utilized to monitor the conditions of the eye 1 to ensure that the changes effected by the eye therapy are stable. In particular, the 3D voxel data can be determined and analyzed after a cross-linking eye therapy procedure to confirm that the strengthening of the corneal tissue is stable and/or identify potential issues with the stability of the corneal tissue strengthening.

In the example system 10 illustrated and described above with respect to FIGS. 1 and 3, the spectrometer 300 measures the scattered light received from the CSM head 200, 200′ with a VIPA 305 and a line scan camera 315, which can employ an electron multiplying charge-coupled device (EMCCD) camera. While a EMCCD camera is a highly sensitive sensor that is well suited for Brillouin imaging, EMCCD cameras are sensitive over a broad range of wavelengths that are not needed for Brillouin microscopy. It has been discovered that another approach can provide improved response times and a lower cost compared to EMCCD cameras. In particular, it has been discovered that a photomultiplier (PMT) can be utilized instead of the VIPA and line scan camera employed in the system 10 described above.

FIG. 6 illustrates aspects of an alternative example spectrometer 300′, which can be used with the system 10. The spectrometer 300′ includes a PMT 380′ with a narrow entrance slit. In the illustrated example, the PMT 380′ is stationary while the light beam to be analyzed is scanned from an imaging lens 385′ across a face of the PMT 380′. More particularly, a scanning mechanism 305′ (e.g., a galvo scanner, polygonal scanner, etc.) can be placed after the imaging lens 385′ to direct the light from the imaging lens 385′ such that it focuses on the PMT 380′. A slit of pre-calculated width is placed on the PMT entrance. As the scanning mechanism 305′ actuates, different peaks of the incident light signal are scanned across the entrance slit.

According to some non-limiting examples, a galvo scanner can be employed as the scanning mechanism 305′ with a scan rate as fast as approximately 14 kHz. Typical rise times of the PMT 380′ can be of the order of 30 ns. Thus, in such examples, the PMT 380′ can provide a readout of about 2380 points per sweep. Accordingly, the galvo scanner and PMT 380′ provide sufficient resolution to measure and calculate the Brillouin shift. It is contemplated that the data rates may be increased further by using a polygonal scanner (which may have a scan rate of approximately 25 kHz).

Additionally, it has been found that a PMT 380′ based spectrometer 300′ such as the example illustrated in FIG. 6 can also enhance the signal-to-noise ratio (e.g., by using a boxcar integrator). In particular, by recording multiple sweeps at the same spatial location on the eye 1 and using a boxcar integrator, the signal-to-noise ratio can be increased.

While the PMT 380′ based spectrometer 300′ is described above employs a scanning mechanism 305′ to scan the light over the face of the PMT 380′, it is contemplated that, according to alternative aspects of the present invention, the PMT 380′ can be scanned spatially to acquire the Brillouin signal spread along a line.

The embodiments above propose various configurations for a spectrometer system for separating the frequencies of light scattered by an into the Brillouin, Rayleigh, and Raman peaks. It is understood that aspects of the present invention may employ a spectrometer system that uses any appropriate technique. In general, the spectrometer system may use a VIPA, interferometer, grating, or grazing incidence grating, which may be used in combination with a line scan camera with either physical or narrow bandwidth filters. These images may then be reconstructed to achieve the three dimensional mapping as described further above.

Although the example systems and methods described herein may be directed to measuring biomechanical properties of the eye to plan, implement, and assess treatments of the eye, it is contemplated that aspects of the present invention may apply to analysis involving other body parts. For example, aspects of the system 1010 described above may be employed in the field of cardiology where the cardio-vasculature is imaged. In such an application, the system may include a sample arm fiber that is coupled to a rotating fiber that is placed down a catheter. A 360 degree image of the lumen of the vessel is obtained. The fiber is then slowly withdrawn to obtain a 3D mapping of the vessel.

The present disclosure includes systems having processors (sometimes considered controllers) for providing various functionality to process information and determine results based on inputs. Generally, the processors (such as the processors 5 described throughout the present disclosure and illustrated in the figures) may be implemented as a combination of hardware and software elements. The hardware aspects may include combinations of operatively coupled hardware components including microprocessors, logical circuitry, communication/networking ports, digital filters, memory, or logical circuitry. The processor may be adapted to perform operations specified by a computer-executable code, which may be stored on a computer readable medium. The processors 5 may be implemented in any device, system, or subsystem to provide functionality and operation according to aspects of the present invention.

The processor(s) 5 may be a programmable processing device, such as an external conventional computer or an on-board field programmable gate array (FPGA) or digital signal processor (DSP), that executes software, or stored instructions. In general, physical processors and/or machines employed by embodiments of the present disclosure for any processing or evaluation may include one or more networked or non-networked general purpose computer systems, microprocessors, field programmable gate arrays (FPGA's), digital signal processors (DSP's), micro-controllers, and the like, programmed according to the teachings of the example embodiments of the present disclosure, as is appreciated by those skilled in the computer and software arts. The physical processors and/or machines may be externally networked with image capture device(s) (e.g., the image capture device 265′), or may be integrated to reside within the image capture device. Appropriate software can be readily prepared by programmers of ordinary skill based on the teachings of the exemplary embodiments, as is appreciated by those skilled in the software art. In addition, the devices and subsystems of the exemplary embodiments can be implemented by the preparation of application-specific integrated circuits or by interconnecting an appropriate network of conventional component circuits, as is appreciated by those skilled in the electrical art(s). Thus, the exemplary embodiments are not limited to any specific combination of hardware circuitry and/or software.

Stored on any one or on a combination of computer readable media, the example embodiments of the present disclosure may include software for controlling the devices and subsystems of the exemplary embodiments, for driving the devices and subsystems of the example embodiments, for enabling the devices and subsystems of the exemplary embodiments to interact with a human user, and the like. Such software can include, but is not limited to, device drivers, firmware, operating systems, development tools, applications software, and the like. Such computer readable media further can include the computer program product of an embodiment of the present disclosure for performing all or a portion (if processing is distributed) of the processing performed in implementations. Computer code devices of the example embodiments of the present disclosure can include any suitable interpretable or executable code mechanism, including but not limited to scripts, interpretable programs, dynamic link libraries (DLLs), Java classes and applets, complete executable programs, and the like. Moreover, parts of the processing of the exemplary embodiments of the present disclosure can be distributed for better performance, reliability, cost, and the like.

The processor(s) 5 may include, or be otherwise combined with, computer-readable media 6. Some forms of computer-readable media may include, for example, a floppy disk, a flexible disk, hard disk, magnetic tape, any other suitable magnetic medium, a CD-ROM, CDRW, DVD, any other suitable optical medium, punch cards, paper tape, optical mark sheets, any other suitable physical medium with patterns of holes or other optically recognizable indicia, a RAM, a PROM, an EPROM, a FLASH-EPROM, any other suitable memory chip or cartridge, a carrier wave or any other suitable medium from which a computer can read.

While the present invention has been described with reference to one or more particular embodiments, those skilled in the art will recognize that many changes may be made thereto without departing from the spirit and scope of the present invention. Each of these embodiments and obvious variations thereof is contemplated as falling within the spirit and scope of the invention. It is also contemplated that additional embodiments according to aspects of the present invention may combine any number of features from any of the embodiments described herein. 

We claim:
 1. A system for measuring biomechanical properties of the eye to at least one of plan, implement, or assess treatments of the eye, the eye having an iris and a cornea, the system comprising: a biomechanical measurement system, including: a light source configured to provide an incident light, a confocal microscopy system configured to direct the incident light at a plurality of sections of the cornea, the incident light being scattered by the plurality of sections of the corneal tissue, and a spectrometer configured to receive the scattered light and process frequency characteristics of the received scattered light to measure a Brillouin frequency shift in the scattered light, the biomechanical measurement system being configured to generate biomechanical data based on the measured Brillouin frequency shift; a corneal topography measurement system configured to measure a corneal topography of the eye and generate corneal topography data indicative of the measured corneal topography; an iris imaging system configured to image the iris and generate iris image data indicative of the imaged iris; and one or more processors communicatively coupled to the biomechanical system, the corneal topography system, and the iris imaging system, the one or more processors including a processor clock; and one or more memory devices storing instructions that, when executed by the one or more processors, cause the one or more processors to: generate time stamp data, based on the processor clock, for each of the biomechanical data, the corneal topography data, and the iris image data; store the biomechanical data with the associated time stamp data in the one or more memory devices; store the corneal topography data with the associated time stamp data in the one or more memory devices; store the iris image data with the associated time stamp data in the one or more memory devices; for each of the biomechanical data, determine which of the iris image data has the same associated time stamp data; for each of the corneal topography data, determine which of the iris image data has the same associated time stamp data; generate three-dimensional voxel data by correlating each of the biomechanical data with each of the corneal topography data determined to have the same associated iris image data, each of the three-dimensional voxel data including an indication of at least one of the biomechanical data, at least one of the corneal topography data, and at least one of the iris image data.
 2. The system according to claim 1, wherein the instructions further cause the one or more processors to determine a treatment plan based on the three-dimensional voxel data.
 3. The system according to claim 2, further comprising an eye treatment system configured to apply an eye therapy to the eye, the eye treatment system including an eye tracking device configured to monitor the iris, the eye treatment system being configured to be automatically oriented and aligned relative to eye based on the treatment plan and the monitoring of the iris by the eye tracking device.
 4. The system according to claim 2, wherein the instructions cause the one or more processors to generate additional three-dimensional voxel data during eye treatment based on the treatment plan.
 5. The system according to claim 4, wherein the instructions cause the one or more processors to iteratively adjust the treatment plan based on the additional three-dimensional voxel data.
 6. The system according to claim 2, wherein the instructions cause the one or more processors to generate additional three-dimensional voxel data after eye treatment based on the treatment plan.
 7. The system according to claim 1, wherein the corneal topography system includes a plurality of stereoscopic cameras.
 8. The system according to claim 1, wherein one or more components of each of the biomechanical measurement system, the corneal topography system, and the iris imaging system are located in a confocal microscopy scan head.
 9. The system according to claim 1, wherein the scattered light includes one or more Brillouin-scattered light frequencies and a Rayleigh-scattered light frequency, the biomechanical measurement system further including a virtual image phased array (VIPA) that is configured to separate Rayleigh-scattered light frequency from the one or more Brillouin-scattered light frequencies and a line scan camera configured to measure the scattered light from the VIPA.
 10. The system according to claim 1, wherein the spectrometer includes scanning mechanism and a photomultiplier (PMT), the PMT having a narrow entrance slit, the scanning mechanism being configured to scan the scattered light across a face of the PMT such that a plurality of different peaks of the scattered light are scanned across the entrance slit of the PMT.
 11. The system of claim 1, wherein the biomechanical measurement system further includes a filter or attenuating device configured to block or attenuate a Rayleigh peak frequency of the scattered light.
 12. The system according to claim 11, wherein the filter or attenuating device includes a Rubidium vapor cell tuned to block the Rayleigh peak frequency.
 13. The system according to claim 1, wherein the biomechanical measurement system includes an optical fiber, a modulated fiber Bragg grating (FBG), and a radio frequency source, the scattered light being directed from the confocal microscopy system to the spectrometer via the optical fiber, the radio frequency source being configured to modulate the FBG to identify Brillouin or Raman frequencies in the scattered light.
 14. The system according to claim 13, wherein the beat frequency identifies a Stokes Brillouin peak and an Anti-Stokes Brillouin peak, the Brillouin frequency shift being determined from the Stokes Brillouin peak and an Anti-Stokes Brillouin peak.
 15. A system that determines biomechanical properties of corneal tissue, comprising: a light source configured to provide an incident light; a confocal microscopy system configured to scan the incident light across a plurality of cross-sections of the corneal tissue, the incident light being reflected by the plurality of cross-sections of corneal tissue as scattered light; a filter or attenuating device configured to block or attenuate the Rayleigh peak frequency of the scattered light; a spectrometer configured to receive the scattered light and process frequency characteristics of the received scattered light to determine a Brillouin frequency shift in response to the Rayleigh peak frequency being blocked or attenuated by the filter or attenuating device; and a processor configured to generate a three-dimensional profile of the corneal tissue according to the determined Brillouin frequency shift, the three-dimensional profile providing an indicator of one or more biomechanical properties of the corneal tissue.
 16. A method for measuring biomechanical properties of the eye to at least one of plan, implement, or assess treatments of the eye, the eye having an iris and a cornea, the method comprising: directing an incident light from a light source, via a confocal microscopy system, at plurality of sections of the cornea, the incident light being scattered by the plurality of sections of the corneal tissue; receiving the scattered light in a spectrometer; processing frequency characteristics of the received scattered light to measure a Brillouin frequency shift in the scattered light; determining biomechanical data based on the measured Brillouin frequency shift; measuring a corneal topography of the eye; determining corneal topography data indicative of the measured corneal topography; imaging, via an image capture device, the iris; determining iris image data indicative of the imaged iris; determining, based on a processor clock provided by one or more processors, time stamp data for each of the biomechanical data, the corneal topography data, and the iris image data; storing the biomechanical data with the associated time stamp data in one or more memory devices; storing the corneal topography data with the associated time stamp data in the one or more memory devices; storing the iris image data with the associated time stamp data in the one or more memory devices; for each of the biomechanical data, determining which of the iris image data has the same associated time stamp data; for each of the corneal topography data, determining which of the iris image data has the same associated time stamp data; and determining three-dimensional voxel data by correlating each of the biomechanical data with each of the corneal topography data determined to have the same associated iris image data, each of the three-dimensional voxel data including an indication of at least one of the biomechanical data, at least one of the corneal topography data, and at least one of the iris image data.
 17. The method according to claim 16, further comprising determining a treatment plan based on the three-dimensional voxel data.
 18. The method according to claim 17, further comprising: applying an eye treatment based on the treatment plan to the eye with an eye treatment system, the eye treatment system including an eye tracking device configured to monitor the iris, monitoring the iris using the eye tracking device; and automatically orienting and aligning the application of the eye treatment relative to eye based on the treatment plan and the monitoring of the iris by the eye tracking device.
 19. The method according to claim 18, further comprising: determining additional three-dimensional voxel data during the application of the eye treatment based on the treatment plan; and iteratively adjust the treatment plan based on the additional three-dimensional voxel data.
 20. The method according to claim 17, further comprising determining additional three-dimensional voxel data after the application of the eye treatment based on the treatment plan. 